U.S. patent application number 15/772273 was filed with the patent office on 2018-11-08 for intraocular lens material.
This patent application is currently assigned to MENICON CO., LTD. The applicant listed for this patent is MENICON CO., LTD. Invention is credited to Hiroko NOMURA, Tatsuya OJIO, Yuya SUGANUMA.
Application Number | 20180318464 15/772273 |
Document ID | / |
Family ID | 61016952 |
Filed Date | 2018-11-08 |
United States Patent
Application |
20180318464 |
Kind Code |
A1 |
SUGANUMA; Yuya ; et
al. |
November 8, 2018 |
INTRAOCULAR LENS MATERIAL
Abstract
An intraocular lens material disclosed in the present
description includes an aromatic ring-containing acrylate
structural unit, an alkoxyalkyl methacrylate structural unit
including an alkoxy group having 4 or less carbon atoms, a
hydrophilic structural unit based on a hydrophilic monomer, and a
cross-linking structural unit based on a cross-linkable
monomer.
Inventors: |
SUGANUMA; Yuya;
(Owariasahi-city, JP) ; NOMURA; Hiroko;
(Nagoya-city, JP) ; OJIO; Tatsuya; (Kasugai-city,
JP) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
MENICON CO., LTD |
Nagoya-shi, Aichi |
|
JP |
|
|
Assignee: |
MENICON CO., LTD
Nagoya-shi, Aichi
JP
|
Family ID: |
61016952 |
Appl. No.: |
15/772273 |
Filed: |
July 27, 2017 |
PCT Filed: |
July 27, 2017 |
PCT NO: |
PCT/JP2017/027176 |
371 Date: |
April 30, 2018 |
Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61L 27/16 20130101;
A61L 2430/16 20130101; A61L 27/50 20130101; G02B 1/041 20130101;
C08F 222/14 20130101; C08F 220/286 20200201; C08F 220/301 20200201;
C08F 220/30 20130101; G02B 1/043 20130101; A61L 27/16 20130101;
C08L 33/10 20130101; C08F 220/301 20200201; C08F 220/18 20130101;
C08F 220/30 20130101; C08F 220/20 20130101; C08F 222/102 20200201;
C08F 220/301 20200201; C08F 220/18 20130101; C08F 220/1812
20200201; C08F 220/20 20130101; C08F 222/102 20200201; C08F 220/301
20200201; C08F 220/18 20130101; C08F 220/281 20200201; C08F 220/20
20130101; C08F 222/102 20200201; G02B 1/043 20130101; C08L 33/08
20130101; C08L 33/10 20130101; C08F 220/301 20200201; C08F 220/18
20130101; C08F 220/1812 20200201; C08F 220/20 20130101; C08F
222/102 20200201 |
International
Class: |
A61L 27/16 20060101
A61L027/16; A61L 27/50 20060101 A61L027/50; C08F 222/14 20060101
C08F222/14; C08F 220/30 20060101 C08F220/30 |
Foreign Application Data
Date |
Code |
Application Number |
Jul 28, 2016 |
JP |
2016-148426 |
Claims
1-8. (canceled)
9. An intraocular lens material comprising: an aromatic
ring-containing acrylate structural unit; an alkoxyalkyl
methacrylate structural unit including an alkoxyalkyl group having
4 or less carbon atoms; an alkyl acrylate structural unit including
an alkyl group having 1 to 20 carbon atoms, a hydrophilic
structural unit based on a hydrophilic monomer; a cross-linking
structural unit based on a cross-linkable monomer, wherein the
aromatic ring-containing acrylate structural unit is phenoxyethyl
acrylate structural unit, the alkoxyalkyl methacrylate structural
unit is an ethoxyethyl methacrylate structural unit, the alkyl
acrylate structural unit is an ethyl acrylate structural unit, and
a base material consists of the aromatic ring-containing acrylate
structural unit, the alkoxyalkyl methacrylate structural unit and
the alkyl acrylate structural unit, and the base material include
one kind of the aromatic ring-containing monomer.
10. The intraocular lens material according to claim 9, wherein the
alkoxyalkyl methacrylate structural unit is included in an amount
within the range of from 10 parts by mass to 70 parts by mass
inclusive based on 100 parts by mass of the total amount of the
base material.
11. The intraocular lens material according to claim 9, wherein the
alkoxyalkyl methacrylate structural unit is included in an amount
within the range of from 10 parts by mass to 40 parts by mass
inclusive based on 100 parts by mass of the total amount of the
base material.
12. The intraocular lens material according to claim 9, wherein the
hydrophilic structural unit is included in an amount within the
range of from 15 parts by mass to 35 parts by mass inclusive by the
outside ratio based on 100 parts by mass of the total amount of the
base material.
13. The intraocular lens material according to claim 9, wherein the
cross-linking structural unit is included in an amount within the
range of from 2 parts by mass to 4 parts by mass inclusive by the
outside ratio based on 100 parts by mass of the total amount of the
base material.
14. The intraocular lens material according to claim 9, wherein the
alkyl acrylate structural unit is included in an amount within the
range of from 10 parts by mass to 35 parts by mass inclusive based
on 100 parts by mass of the total amount of the base material.
15. The intraocular lens material according to claim 9, wherein the
aromatic ring-containing acrylate structural unit is included in an
amount within the range of from 15 parts by mass to 80 parts by
mass inclusive based on 100 parts by mass of the total amount of
the base material.
16. The intraocular lens material according to claim 9, wherein the
hydrophilic structural unit is a hydroxyethyl methacrylate
structural unit.
17. The intraocular lens material according to claim 9, wherein the
cross-linking structural unit is a butanediol diacrylate structural
unit.
18. The intraocular lens material according to claim 9, wherein the
aromatic ring-containing acrylate structural unit is included in an
amount within the range of from 30 parts by mass to 80 parts by
mass inclusive based on 100 parts by mass of the total amount of
the base material, the alkoxyalkyl methacrylate structural unit is
included in an amount within the range of from 10 parts by mass to
40 parts by mass inclusive based on 100 parts by mass of the total
amount of the base material, the alkyl acrylate structural unit is
included in an amount within the range of from 10 parts by mass to
35 parts by mass inclusive based on 100 parts by mass of the total
amount of the base material.
Description
TECHNICAL FIELD
[0001] The present invention relates to an intraocular lens
material.
BACKGROUND ART
[0002] Progress in small-incision cataract surgery has led to the
development of soft, flexible and foldable materials suitable for
intraocular lenses. In particular, acrylic materials are desirable
because they have a high refractive index and unfold slowly after
insertion into an eye. However, when a material with enhanced shape
recoverability is used for a lens, the elongation percentage of the
lens becomes low. This material is brittle and easily torn when the
lens has, for example, a flaw. To insert a lens into an eye through
a minimum incision, it is preferable to use a material with a large
elongation percentage so that the lens is prevented from cracking
and tearing.
[0003] One previously proposed intraocular lens material is a
polymer obtained by polymerizing polymerizable components including
a hydrophilic monomer such as a hydroxyl group-containing alkyl
(meth)acrylate, a (meth)acrylamide monomer, or an N-vinyl lactam,
and the water absorption percentage of the intraocular lens
material is 1.5 to 4.5% by mass (see, for example, PTL 1). This
intraocular lens material is excellent in flexibility and has a
high refractive index. Therefore, a lens with a reduced thickness
can be provided, and the lens in a folded state can be inserted
through an incision. Moreover, the intraocular lens material has
excellent transparency and can reduce the occurrence of
glistening.
CITATION LIST
Patent Literature
[0004] PTL 1: Japanese Unexamined Patent Application Publication
No. 11-56998
SUMMARY OF THE INVENTION
Technical Problem
[0005] In an acrylic elastomer using the intraocular lens material
in PTL 1, ester moieties may undergo hydrolysis, and dissolution of
a hydrolysate may occur although the amount of dissolution is very
small. There is therefore a need for a material that can provide an
intraocular lens from which only a reduced amount of a hydrolysate
dissolves.
[0006] The present invention has been made in view of the foregoing
circumstances, and it is a primary object to provide an intraocular
lens material from which only a reduced amount of the hydrolysate
dissolves in an aqueous solution.
Solution to Problem
[0007] To achieve the above object, the present inventors have
conducted extensive studies and found that, when an intraocular
lens material containing an acrylate as a base material contains a
specific methacrylate, the amount of a hydrolysate dissolved in an
aqueous solution can be further reduced while the desired
properties of the intraocular lens material are maintained or
improved. Thus, the present invention has been completed.
[0008] Accordingly, an intraocular lens material disclosed in the
present description comprises: an aromatic ring-containing acrylate
structural unit; an alkoxyalkyl methacrylate structural unit
including an alkoxyalkyl group having 4 or less carbon atoms; a
hydrophilic structural unit based on a hydrophilic monomer; and a
cross-linking structural unit based on a cross-linkable
monomer.
[0009] With this intraocular lens material, the amount of a
hydrolysate dissolved from the intraocular lens material in an
aqueous solution can be further reduced. The reason that this
effect is obtained may be, for example, as follows. For example,
methacrylate is a material harder than acrylate because of the
presence of a methyl group but may resist attack by water.
Therefore, hydrolysis resistance may be improved. In the case that
the alkoxyalkyl group having 4 or less carbon atoms is included,
the number of carbon atoms is preferable, and therefore the
intraocular lens material may not be excessively hard and may have
sufficient flexibility. Moreover, the intraocular lens material
containing the alkoxyalkyl group having 4 or less carbon atoms may
be preferred in terms of flexibility, reduction in stickiness, and
the ability to reduce the occurrence of glistening. The alkoxyalkyl
group may be represented by, for example, chemical formula (1).
C.sub.nH.sub.2n+1OC.sub.mH.sub.2m-- ((n+m).ltoreq.4) (1)
BRIEF DESCRIPTION OF DRAWINGS
[0010] FIG. 1 is a side view of an indenter 10 and a jig 11 that
are used for compressive load measurement.
[0011] FIG. 2 is an illustration of a specimen used for elongation
percentage measurement.
DESCRIPTION OF EMBODIMENTS
[0012] An intraocular lens material disclosed in an embodiment
comprises: an aromatic ring-containing acrylate structural unit; an
alkoxyalkyl methacrylate structural unit including an alkoxyalkyl
group having 4 or less carbon atoms; a hydrophilic structural unit
based on a hydrophilic monomer; and a cross-linking structural unit
based on a cross-linkable monomer. This intraocular lens material
contains, as a base material, the aromatic ring-containing acrylate
structural unit and the alkoxyalkyl methacrylate structural unit
including the alkoxyalkyl group having 4 or less carbon atoms. The
intraocular lens material may further contain, as a base material,
an alkyl acrylate structural unit including an alkyl group having 1
to 20 carbon atoms. The base material is component forming the main
structure of the intraocular lens material. As shown in chemical
formula (2), the intraocular lens material may contain, as a base
material, aromatic ring-containing acrylate structural units A,
alkoxyalkyl methacrylate structural units B, and alkyl acrylate
structural units C. In chemical formula (2), a, b, and c are any
integers. The aromatic ring-containing acrylate structural units A,
the alkoxyalkyl methacrylate structural units B, and the alkyl
acrylate structural units C are bonded to a carbon chain in an
arbitrary manner, and adjacent structural units may be the same or
different. A functional group R.sup.1 is an aromatic
ring-containing functional group, and a functional group R.sup.2 is
an alkoxyalkyl group including an alkoxy group and having 4 or less
carbon atoms. A functional group R.sup.3 is an alkyl group having 1
to 20 carbon atoms. As used herein, acrylate having an acryloyl
group and methacrylate having a methacryloyl group are collectively
referred to as "(meth)acrylate." For the sake of convenience of
description, a structural unit included in a polymer is designated
by the name of a corresponding monomer. Monomers exemplified in the
description of a polymer structure have structures in which their
polymerizable groups are bonded to other structural units. For
example, a monomer exemplified as "(meth)acrylate" in the
description of a polymer structure is present as a "(meth)acrylate
structural unit" in the polymer. In this structural unit, another
structural unit is bonded (polymerized) to a double bond of the
(meth) acrylate.
##STR00001##
[0013] In this intraocular lens material, the aromatic
ring-containing acrylate structural unit is a structural unit based
on an aromatic ring-containing acrylate used as a base material
monomer. This aromatic ring-containing acrylate may be a component
having the function of increasing the refractive index of the
intraocular lens material. This aromatic ring-containing acrylate
structural unit may have a phenoxy group, an alkylene group having
2 or less carbon atoms, and an acrylate bond moiety. Examples of
the aromatic ring-containing acrylate include phenoxyethyl
acrylate, phenylethyl acrylate, benzyl acrylate, phenyl acrylate,
and pentabromophenyl acrylate. These may be used alone, or a
mixture of two or more may be used. Of these, at least one of
phenoxyethyl acrylate, phenylethyl acrylate, and benzyl acrylate is
preferred because their effect of increasing the refractive index
is high. Phenoxyethyl acrylate is particularly preferred because it
can further enhance flexibility. Preferably, the amount of the
aromatic ring-containing acrylate is within the range of from 15
parts by mass to 80 parts by mass inclusive based on 100 parts by
mass of the total amount of the base material. More preferably, the
amount of the aromatic ring-containing acrylate is from 30 parts by
mass to 80 parts by mass inclusive based on 100 parts of the base
material because it is desirable that the intraocular lens material
has a high refractive index even in a moistened state.
[0014] In the intraocular lens material, the alkoxyalkyl
methacrylate structural unit including the alkoxyalkyl group having
4 or less carbon atoms is a structural unit based on an alkoxyalkyl
methacrylate used as a base material monomer. The alkoxyalkyl group
in the alkoxyalkyl methacrylate may be, for example, a group
represented by chemical formula (1) above. Examples of the alkoxy
group include a methoxy group and an ethoxy group. Examples of the
alkylene group to which the alkoxy group is bonded include a
methylene group and an ethylene group. The alkoxyalkyl methacrylate
is preferably at least one of methoxyethyl methacrylate and
ethoxyethyl methacrylate and more preferably ethoxyethyl
methacrylate. The amount of the alkoxyalkyl methacrylate is
preferably within the range of from 10 parts by mass to 70 parts by
mass inclusive based on 100 parts by mass of the total amount of
the base material. From the viewpoint that the degree of hydrolysis
can be further reduced and from the viewpoint of ease of folding,
the amount of the alkoxyalkyl methacrylate is more preferably from
20 parts by mass to 40 parts by mass inclusive based on 100 parts
by mass of the base material. An example of the structure of the
intraocular lens material is shown in chemical formula (3). In this
example, the base material is 2-phenoxyethyl acrylate (POEA), ethyl
acrylate (EA), and ethoxyethyl methacrylate (ETMA). In chemical
formula (3), a, b, and c are any integers. The aromatic
ring-containing acrylate structural units A, the alkoxyalkyl
methacrylate structural units B, and the alkyl acrylate structural
units C are bonded to a carbon chain in an arbitrary manner, and
adjacent structural units may be the same or different.
##STR00002##
[0015] In the intraocular lens material, the alkyl acrylate
structural unit including the alkyl group having 1 to 20 carbon
atoms is a structural unit based on an alkyl acrylate used as a
base material monomer. The alkyl acrylate including the alkyl group
having 1 to 20 carbon atoms may be a component having the function
of improving the shape recoverability and flexibility of the
intraocular lens material. Examples of the alkyl acrylate include
straight-chain, branched-chain, and cyclic alkyl acrylates such as
methyl acrylate, ethyl acrylate, propyl acrylate, butyl acrylate,
pentyl acrylate, hexyl acrylate, heptyl acrylate, nonyl acrylate,
stearyl acrylate, octyl acrylate, decyl acrylate, lauryl acrylate,
pentadecyl acrylate, 2-ethylhexyl acrylate, cyclopentyl acrylate,
and cyclohexyl acrylate. Other examples of the alkyl acrylate
include fluorine-containing alkyl (meth)acrylates such as
2,2,2-trifluoroethyl acrylate, 2,2,3,3-tetrafluoropropyl acrylate,
2,2,3,3-tetrafluoro-t-pentyl acrylate, 2,2,3,4,4,4-hexafluorobutyl
acrylate, 2,2,3,4,4,4-hexafluoro-t-hexyl acrylate,
2,3,4,5,5,5-hexafluoro-2,4-bis(trifluoromethyl)pentyl acrylate,
2,2,3,3,4,4-hexafluorobutyl acrylate,
2,2,2,2',2',2'-hexafluoroisopropyl acrylate,
2,2,3,3,4,4,4-heptafluorobutyl acrylate, and
2,2,3,3,4,4,5,5-octafluoropentyl acrylate. These may be used alone,
or a mixture of two or more may be used. Of these, alkyl acrylates
including an alkyl group having 1 to 5 carbon atoms are preferred
because their effect of improving the shape recoverability and
flexibility is high, and ethyl acrylate and butyl acrylate are
particularly preferably used. Preferably, the amount of the alkyl
acrylate is within the range of from 0 parts by mass to 35 parts by
mass inclusive based on 100 parts by mass of the total amount of
the base material. The alkyl acrylate is regarded as one of the
base material but is not necessarily an essential component. In
terms of the flexibility and shape recoverability, the amount of
the alkyl acrylate may be appropriately adjusted at the above
ratio.
[0016] In the intraocular lens material, the hydrophilic structural
unit is a structural unit based on a hydrophilic monomer. The
hydrophilic monomer is a component that provides hydrophilicity to
the intraocular lens material and may be a component having the
function of facilitating a reduction in the occurrence of
glistening in the intraocular lens material. The hydrophilic
monomer may include, for example, at least one of hydroxyl
group-containing alkyl (meth)acrylates including an alkyl group
having 1 to 20 carbon atoms, (meth)acrylamide monomers, and N-vinyl
lactams. An additional hydrophilic monomer other than the above
hydrophilic monomers may be included. Examples of the hydroxyl
group-containing alkyl (meth)acrylate include: hydroxyalkyl
(meth)acrylates such as hydroxyethyl (meth) acrylate, hydroxypropyl
(meth) acrylate, hydroxybutyl (meth)acrylate, and hydroxypentyl
(meth)acrylate; and dihydroxyalkyl (meth)acrylates such as
dihydroxypropyl (meth)acrylate, dihydroxybutyl (meth)acrylate, and
dihydroxypentyl (meth)acrylate. Examples of the (meth)acrylamide
monomer include N,N-dialkyl(meth)acrylamides such as
N,N-dimethyl(meth)acrylamide, N,N-diethyl(meth)acrylamide, and
N,N-dipropyl(meth)acrylamide; and
N,N-dialkylaminoalkyl(meth)acrylamides such as
N,N-dimethylaminopropyl(meth)acrylamide and
N,N-diethylaminopropyl(meth)acrylamide. Examples of the N-vinyl
lactam include N-vinylpyrrolidone, N-vinylpiperidone, and
N-vinylcaprolactam. Examples of the additional hydrophilic monomer
include diethylene glycol mono(meth)acrylate, triethylene glycol
mono(meth)acrylate, propylene glycol mono(meth)acrylate,
(meth)acrylic acid, 1-methyl-3-methylene-2-pyrrolidinone, maleic
anhydride, maleic acid, maleic acid derivatives, fumaric acid,
fumaric acid derivatives, aminostyrene, and hydroxystyrene. The
above-described hydrophilic monomers may be used alone, or a
mixture of two or more may be used. Among these hydrophilic
monomers, hydroxyl group-containing alkyl (meth)acrylates and
(meth)acrylamide monomers are preferred because their function of
facilitating a reduction in the occurrence of glistening is high,
and 2-hydroxyethyl methacrylate is particularly preferred.
Preferably, the content of the hydrophilic monomer is within the
range of from 15 parts by mass to 35 parts by mass inclusive by the
outside ratio based on 100 parts by mass of the total amount of the
base material. When the content of the hydrophilic monomer is
within this range, the effect of facilitating a reduction in the
occurrence of glistening can be sufficiently obtained, and no
significant burden and difficulty arise when the intraocular lens
material in a dry state is folded.
[0017] In the intraocular lens material, the cross-linking
structural unit is a structural unit based on a cross-linkable
monomer. The cross-linkable monomer may be a component that has the
function of controlling the flexibility of the intraocular lens
material, the function of imparting good mechanical properties, the
function of further improving the shape recoverability, and the
function of improving copolymerizability of the polymerizable
components such as the hydrophilic monomer and other polymerizable
monomers. Examples of the cross-linkable monomer include butanediol
di(meth)acrylate, ethylene glycol di(meth)acrylate, diethylene
glycol di(meth)acrylate, triethylene glycol di(meth)acrylate,
propylene glycol di(meth)acrylate, dipropylene glycol
di(meth)acrylate, diallyl fumarate, allyl (meth)acrylate, vinyl
(meth)acrylate, trimethylolpropane tri(meth)acrylate,
methacryloyloxyethyl (meth)acrylate, divinylbenzene, diallyl
phthalate, diallyl adipate, triallyl diisocyanate,
.alpha.-methylene-N-vinylpyrrolidone, 4-vinylbenzyl (meth)acrylate,
3-vinylbenzyl (meth)acrylate,
2,2-bis((meth)acryloyloxyphenyl)hexafluoropropane,
2,2-bis((meth)acryloyloxyphenyl)propane,
1,4-bis(2-(meth)acryloyloxyhexafluoroisopropyl)benzene,
1,3-bis(2-(meth)acryloyloxyhexafluoroisopropyl)benzene,
1,2-bis(2-(meth)acryloyloxyhexafluoroisopropyl)benzene,
1,4-bis(2-(meth)acryloyloxyisopropyl)benzene,
1,3-bis(2-(meth)acryloyloxyisopropyl)benzene, and
1,2-bis(2-(meth)acryloyloxyisopropyl)benzene. These may be used
alone, or a mixture of two or more may be used. Among these
cross-linkable monomers, at least one of butanediol
di(meth)acrylate and ethylene glycol di(meth)acrylate is
particularly preferred because the effect of controlling the
flexibility, the effect of imparting good mechanical properties,
and the effect of improving the shape recoverability and
copolymerizability are high. Preferably, the content of the
cross-linkable monomer is within the range of from 2 parts by mass
to 4 parts by mass inclusive by the outside ratio based on 100
parts by mass of the total amount of the base material. The content
is preferably 2 parts by mass or more from the viewpoint of
imparting the shape recoverability and reducing the occurrence of
glistening. The content is preferably 4 parts by mass or less
because the intraocular lens material can have an elongation
percentage high enough to allow insertion from a small
incision.
[0018] The intraocular lens material may contain other additional
components such as an ultraviolet absorber and a coloring agent.
Examples of the ultraviolet absorber include: benzophenones such as
2-hydroxy-4-methoxybenzophenone and 2-hydroxy-4-octoxybenzophenone;
benzotriazoles such as
2-(2'-hydroxy-5'-methacryloxyethyleneoxy-t-butylphenyl)-5-methyl-benzotri-
azole, 2-(2'-hydroxy-5'-methylphenyl)benzotriazole, and
5-chloro-2(3'-t-butyl-2'-hydroxy-5'-methylphenyl)benzotriazole;
salicylic acid derivatives; and hydroxyacetophenone derivatives.
Preferably, the amount of the ultraviolet absorber added is, for
example, within the range of from 0.05 parts by mass to 3 parts by
mass inclusive by the outside ratio based on 100 parts by mass of
the total amount of the base material. For example, to correct
cyanopsia, it is preferable to use a yellow or orange coloring
agent. Examples of the coloring agent include: a dye described in
Japanese Unexamined Patent Application Publication No. 2006-291006;
oil-soluble dyes such as CI Solvent Yellow and CI Solvent Orange
listed in the Color Index International (CI); disperse dyes such as
CI Disperse Yellow and CI Disperse Orange listed in the Color Index
International (CI); and vat dyes. Preferably, the amount of the
coloring agent added is within the range of from 0.01 parts by mass
to 3 parts by mass inclusive by the outside ratio based on 100
parts by mass of the total amount of the base material.
[0019] For example, a radical polymerization initiator or a
photopolymerization initiator may be added for polymerization to
obtain the intraocular lens material. For example, a polymerization
method in which a radical polymerization initiator is added
followed by heating or irradiation with electromagnetic waves such
as microwaves, ultraviolet radiation, or radiation (.gamma.
radiation) may be used. Examples of the radical polymerization
initiator include azobisisobutyronitrile,
azobisdimethylvaleronitrile, benzoyl peroxide, t-butyl
hydroperoxide, and cumene hydroperoxide. When a light beam, for
example, is used for polymerization, it is preferable to further
add a photopolymerization initiator or a sensitizer. Examples of
the photopolymerization initiator include: benzoin-based compounds
such as methyl orthobenzoyl benzoate; phenone-based compounds such
as 2-hydroxy-2-methyl-1-phenylpropane-1-one; thioxanthone-based
compounds such as 1-hydroxycyclohexyl phenyl ketone,
1-phenyl-1,2-propanedione-2-(o-ethoxycarbonyl)oxime, and
2-chlorothioxanthone; dibenzosuberone; 2-ethylanthraquinone;
benzophenone acrylate; benzophenone; and benzil. To allow the
polymerization reaction to proceed at a sufficient rate, the amount
of the polymerization initiator or sensitizer used is preferably
within the range of from 0.01 parts by mass to 2 parts by mass
inclusive by the outside ratio based on 100 parts by mass of the
total amount of the base material. The intraocular lens material of
the present invention may be formed into an intraocular lens using,
for example, lathing or molding.
[0020] In the intraocular lens material, glistening is less likely
to occur. When the material in the form of a lens is evaluated
using an experimental method described in the present description,
the number of glistening spots per a lens is preferably 15 or less.
When the material in the form of a plate is evaluated using the
above method, the number of glistening spots per a plate is
preferably 6 or less and more preferably 2 or less.
[0021] The intraocular lens material has an elongation percentage
high enough to allow insertion from a small incision. Specifically,
when the material is evaluated using an experimental method
described in the present description, the elongation percentage is
preferably 170% or more. In terms of the shape recoverability of
the intraocular lens material, the elongation percentage is
preferably 600% or less.
[0022] In the intraocular lens material, the dissolution rate of
phenoxyethyl alcohol (POEtOH), which is a hydrolysate of the
material, after the material has been stored in water at
100.degree. C. for 30 days is preferably 0.13% by mass or less and
more preferably 0.10% by mass or less. In the intraocular lens
material, the dissolution rate of POEtOH from the material after
the material has been stored in water at 100.degree. C. for 60 days
is preferably 0.80% by mass or less and more preferably 0.70% by
mass or less. In the intraocular lens material, the dissolution
rate of POEtOH from the material after the material has been stored
in water at 100.degree. C. for 90 days is preferably 3.30% by mass
or less and more preferably 2.80% by mass or less. The smaller the
dissolution rate, the more preferred.
[0023] In the intraocular lens material, the water absorption
percentage (% by mass) of the material is preferably within the
range of from 1.5% by mass to 4.5% by mass inclusive. When the
water absorption percentage is 1.5% by mass or more, the occurrence
of glistening can be reduced. When the water absorption percentage
is 4.5% by mass or less, a reduction in flexibility and a reduction
in shape recoverability can be suppressed. As described above, the
intraocular lens material of the present invention is excellent in
flexibility and has a high refractive index. Therefore, a lens with
a reduced thickness can be provided, and the lens in a folded state
can be inserted through a small incision. Moreover, the intraocular
lens material has excellent transparency and can reduce the
occurrence of glistening.
[0024] With the intraocular lens material in the present embodiment
described above in detail, the amount of the hydrolysate dissolved
from the intraocular lens material in an aqueous solution can be
reduced. The reason that the above effect is obtained is that, for
example, the alkoxyalkyl methacrylate including the alkoxyalkyl
group having 4 or less carbon atoms is included in addition to the
acrylates used as a base material. Generally, methacrylate is a
material harder than acrylate because of the presence of a methyl
group but resists attack by water, and therefore hydrolysis
resistance may be improved. When the number of methacrylate
structural units is increased, glistening often occurs easily.
Although this mechanism is not clear, since the polymerization rate
of acrylic differs from the polymerization rate of methacrylic,
phase separation easily occurs, so that glistening seems to occur
easily. However, in the intraocular lens material in the present
embodiment, the alkoxyalkyl methacrylate is used as methacrylate,
so that the ability to reduce the occurrence of glistening does not
seem to be lost. Moreover, the alkoxyalkyl methacrylate having 4 or
less carbon atoms is preferred in terms of flexibility, reduction
in stickiness, and the ability to reduce the occurrence of
glistening.
[0025] The present invention is not limited to the above-described
embodiment. It will be appreciated that the invention can be
embodied in various forms so long as they fall within the technical
scope of the invention.
EXAMPLES
[0026] Examples in which the intraocular lens of the present
invention was actually produced will be described as Experimental
Examples. Experimental Examples 7 to 14, 18, 20, 21, 23, 24, 26 to
29, 31, 32, 34, 35, 37 to 43, 45 to 53, 55, 57, 59, and 60
correspond to Examples of the present invention. Experimental
Examples 1 to 6, 15 to 17, 19, 22, 25, 30, 33, 36, 44, 54, 56, and
58 correspond to Comparative Examples. The present invention is not
limited to the following Examples, and it will be appreciated that
the invention can be embodied in various forms so long as they fall
within the technical scope of the invention.
[0027] [Components Used]
[0028] Abbreviations for the compounds used in the Experimental
Examples are shown below.
<Base Material>
[0029] POEA: 2-phenoxyethyl acrylate [0030] EA: ethyl acrylate
[0031] POEMA: phenoxyethyl methacrylate [0032] EMA: ethyl
methacrylate [0033] BMA: butyl methacrylate [0034] EHMA: ethylhexyl
methacrylate [0035] LMA: lauryl methacrylate [0036] MTMA:
methoxyethyl methacrylate [0037] ETMA: ethoxyethyl methacrylate
<Hydrophilic Monomer>
[0037] [0038] HEMA: 2-hydroxyethyl methacrylate
<Cross-Linkable Monomer>
[0038] [0039] BDDA: 1,4-butanediol diacrylate
[0040] [Preparation of Plate-Shaped and Lens-Shaped Intraocular
Lens Materials]
[0041] Polymerizable components shown in Table 1 were mixed with
0.5 parts by mass of 2,2'-azobis(2,4-dimethylvaleronitrile) as a
polymerization initiator by the outside ratio based on 100 parts by
mass of the total amount of the base material. The mixture was
poured into a mold having a desired lens shape. The mold was placed
in an oven at 80.degree. C., and the mixture was subjected to heat
polymerization molding for 40 minutes. The polymer obtained was
removed from the mold and subjected to elution treatment. Then the
resulting polymer was dried in an oven at 60.degree. C., and a
lens-shaped intraocular lens material (one of Experimental Examples
1 to 14) was thereby obtained. Similarly, polymerizable components
shown in Tables 2 to 4 were used and poured into a mold having a
desired plate shape, and the same procedure as described above was
repeated to obtain a plate-shaped intraocular lens material (one of
Experimental Examples 15 to 60). Plate specimens with the same
number (composition) but two different thicknesses were prepared
according to the required measurement items. A plate with a
thickness of 0.5 mm or 0.8 mm described later is a plate prepared
using a mold with a 0.5 mm or 0.8 mm-thick spacer. Each dried plate
was punched into a measurement plate with a diameter of 6 mm or 8
mm according to a test purpose.
TABLE-US-00001 TABLE 1 Hydrophilic Base material monomer
Cross-linkable POEA EA POEMA EHMA LMA ETMA HEMA monomer Specimen
Parts Parts Parts Parts Parts Parts Parts by BDDA (Lens) by mass by
mass by mass by mass by mass by mass mass Parts by mass
Experimental 40 20 40 15 4 example 1 Experimental 60 40 15 4
example 2 Experimental 60 20 20 15 4 example 3 Experimental 60 20
20 15 4 example 4 Experimental 30 40 30 15 4 example 5 Experimental
70 30 15 3 example 6 Experimental 60 40 15 2 example 7 Experimental
60 20 20 15 2 example 8 Experimental 60 20 20 15 2.5 example 9
Experimental 60 20 20 15 3 example 10 Experimental 60 15 25 15 2.5
example 11 Experimental 60 15 25 15 3 example 12 Experimental 60 10
30 15 2.5 example 13 Experimental 60 10 30 15 3 example 14
TABLE-US-00002 TABLE 2 Hydrophilic Cross-linkable Base material
monomer monomer POEA EA EMA BMA LMA MTMA ETMA HEMA BDDA Specimen
Parts Parts Parts Parts Parts Parts Parts Parts by Parts by (Plate)
by mass by mass by mass by mass by mass by mass by mass mass mass
Experimental 60 40 15 4 example 15 Experimental 60 40 15 4 example
16 Experimental 60 20 20 15 4 example 17 Experimental 60 40 15 4
example 18 Experimental 60 40 15 4 example 19 Experimental 60 20 20
15 4 example 20 Experimental 60 40 15 4 example 21
TABLE-US-00003 TABLE 3 Hydrophilic Base material monomer
Cross-linkable POEA EA ETMA HEMA monomer Specimen Parts Parts Parts
Parts by BDDA (Plate) by mass by mass by mass mass Parts by mass
Experimental 60 40 15 3 example 22 Experimental 60 20 20 15 3
example 23 Experimental 60 40 15 3 example 24 Experimental 60 40 15
2 example 25 Experimental 60 30 10 15 2 example 26 Experimental 60
20 20 15 2 example 27 Experimental 60 15 25 15 2 example 28
Experimental 60 40 15 2 example 29 Experimental 60 40 20 4 example
30 Experimental 60 20 20 20 4 example 31 Experimental 60 40 20 4
example 32 Experimental 60 40 20 3 example 33 Experimental 60 20 20
20 3 example 34 Experimental 60 40 20 3 example 35 Experimental 60
40 20 2 example 36 Experimental 60 20 20 20 2 example 37
Experimental 60 40 20 2 example 38
TABLE-US-00004 TABLE 4 Hydrophilic Base material monomer
Cross-linkable POEA EA ETMA HEMA monomer Specimen Parts Parts Parts
Parts by BDDA (Plate) by mass by mass by mass mass Parts by mass
Experimental 60 20 20 25 4 example 39 Experimental 60 40 25 4
example 40 Experimental 50 50 25 4 example 41 Experimental 40 60 25
4 example 42 Experimental 30 70 25 4 example 43 Experimental 20 80
25 4 example 44 Experimental 60 20 20 25 3 example 45 Experimental
60 40 25 3 example 46 Experimental 60 20 20 25 2 example 47
Experimental 60 40 25 2 example 48 Experimental 60 40 35 4 example
49 Experimental 50 50 35 4 example 50 Experimental 40 60 35 4
example 51 Experimental 60 40 40 4 example 52 Experimental 60 40 45
4 example 53 Experimental 60 40 60 4 example 54 Experimental 60 30
10 20 3 example 55 Experimental 60 40 25 3 example 56 Experimental
60 30 10 25 3 example 57 Experimental 60 40 25 2 example 58
Experimental 60 30 10 25 2 example 59 Experimental 60 10 30 25 2
example 60
[0042] <Measurement of Physical Properties>
(Hydrolysis Treatment)
[0043] A specimen was dried at 60.degree. C. in advance, and its
pre-treatment mass W.sub.0 was measured. 50 mL of distilled water
was placed in a 100 mL pressure bottle, and the specimen was
immersed therein. The pressure bottle was placed in an incubator at
100.degree. C. and stored therein. Ten plates with a diameter of 6
mm and a thickness of 0.5 mm were used as the specimen. The tare
mass W.sub.01 of the bottle, the mass W.sub.02 of the bottle after
the addition of distilled water, and the mass W.sub.03 of the
bottle after the immersion of the specimen were recorded.
[0044] (Dissolution Rate of POEtOH)
[0045] The concentration of phenoxyethyl alcohol (POEtOH,
hydrolysate of POEA) in the extraction solution and the dissolution
rate of POEtOH after 30 days of the hydrolysis treatment were
determined using the following procedure. The mass W.sub.11 of the
bottle before collection of the extraction solution was recorded.
Then the extraction solution was collected from the bottle, and the
mass W.sub.12 of the bottle after the collection of the extraction
solution was recorded. The collected extraction solution, standard
solutions, and a blank (distilled water) were analyzed using HPLC.
After the analysis, the chromatogram of the distilled water was
subtracted from the chromatograms of the collected extraction
solution and the standard solutions to perform baseline correction.
The area of the peak of POEtOH in each of the corrected
chromatograms was calculated. A calibration curve was produced from
the POEtOH concentrations and peak areas of the standard solutions.
The concentration of POEtOH in the extraction solution was
calculated using the area of the peak of POEtOH in the extraction
solution and the calibration curve obtained. The dissolution rate
of POEtOH per 1 g of the specimen was calculated from formula (1)
below using the POEtOH concentration obtained. The volume of the
extraction solution was calculated from formula (2). The volume of
the extraction solution was calculated based on the following
premises. The change in the mass of the specimen during heating at
100.degree. C. is negligibly smaller than the change in the mass of
the extraction solution. Since the most part of the extraction
solution is water, the computation can be performed using 1 g/mL as
the density of the extraction solution without any problem. After
the analysis of the extraction solution after 30 days of the
hydrolysis treatment, the bottle was again placed in the incubator
at 100.degree. C. After a total of 60 days of the hydrolysis
treatment, the extraction solution was again collected. The same
procedure as that preformed after 30 days of the treatment was
repeated. Specifically, the mass W.sub.21 of the bottle before
collection of the extraction solution was recorded. Then the
concentration of POEtOH in the extraction solution was quantified
by HPLC analysis, and the dissolution rate of POEtOH was calculated
from formula (3). The volume of the extraction solution was
calculated from formula (4). Similarly, the dissolution rate of
POEtOH after a total of 90 days of the hydrolysis treatment was
calculated.
The dissolution rate of POEtOH (%)=the concentration of POEtOH in
the extraction solution (ppm).times.10.sup.-6.times.the volume of
the extraction solution V.sub.1S (mL)/pre-treatment mass W.sub.0
(g).times.100 Formula (1)
The volume of the extraction solution V.sub.1S
(mL.apprxeq.g)=[W.sub.02 (g)-W.sub.01 (g)]-[W.sub.03 (g)-W.sub.11
(g)] Formula (2)
The dissolution rate of POEtOH (%)=the concentration of POEtOH in
the extraction solution (ppm).times.10.sup.-6.times.the volume of
the extraction solution V.sub.2S (mL)/pre-treatment mass W.sub.0
(g).times.100 Formula (3)
The volume of the extraction solution V.sub.2S
(mL.apprxeq.g)=V.sub.1S (mL.apprxeq.g)-[W.sub.11 (g)-W.sub.12
(g)]-[W.sub.12 (g)-W.sub.21 (g)] Formula (4)
[0046] (Glistening)
[0047] In the measurement of glistening, lens-shaped specimens with
a diameter of 6 mm and a center thickness of 0.8 mm.+-.0.1 mm or
plate specimens with a diameter of 6 mm and a thickness of 0.5 mm
were used. The lens-shaped specimens were immersed in water at
35.degree. C. for 17 hours or longer and then immersed in water at
25.degree. C. for 2 hours, and the appearance was observed under a
stereoscopic microscope. The plate specimens were immersed in water
at 35.degree. C. for 22 hours and then immersed in water at
25.degree. C. for 2 hours, and the appearance was observed under a
stereoscopic microscope. In each experimental example, the
observation of the appearance was performed on 2 or 3 specimens,
and the number of glistening spots (bright spots) formed was
examined. The magnification used was about 10.times. to about
60.times.. The magnification was appropriately adjusted within the
above range so that the glistening was easily observed.
[0048] (Water Absorption Percentage)
[0049] The mass of each specimen in an equilibrium moisture state
and its mass in a dry state were measured, and the water absorption
percentage (mass %) of the specimen was calculated. The water
absorption percentage was calculated from formula (5) below using
the mass W.sub.w of the specimen in the equilibrium moisture state
at 25.degree. C. and the mass W.sub.d of the specimen in the dry
state. Five plates with a diameter of 6 mm and a thickness of 0.8
mm were used as the specimens.
The water absorption percentage (mass
%)=(W.sub.w-W.sub.d)/W.sub.d.times.100 Formula (5)
[0050] (Refractive Index)
[0051] The refractive index of each specimen was determined using
the Mercury e-line in an Abbe refractometer. The measurement was
performed on the specimen in a dry state (25.degree. C.) or a
moisture state (35.degree. C.). The specimen used was a plate with
a diameter of 6 mm and a thickness of 0.8 mm.
[0052] (Compressive Load (Plate))
[0053] A plate with a diameter of 6 mm and a thickness of 0.5 mm
was compressed and buckled (bending buckling) according to the
following procedure. Then a load value when the specimen was
buckled from 6 mm to 3 mm was measured as a compressive load value.
Before the measurement, the specimen was left to stand in an
environment at 23.degree. C. and 50% RH to control its state. FIG.
1 is a side view of an indenter 10 and a jig 11 used for the
measurement of the compressive load. Each of the indenter 10 and
the jig 11 is made of polyoxymethylene (DURACON) and has a
cylindrical shape. The indenter 10 and the jig 11 were attached to
a creep meter (RE2-33005S manufactured by Yamaden Co., Ltd.). A
double-sided adhesive tape (3M Scotch Brand Tape core series
2-0300) was attached to a specimen placement area on the upper
surface of the jig 11, and the specimen 12 was placed. A specimen
stage (support) with the jig 11 attached thereto was moved up and
down to bring the specimen 12 into contact with the indenter 10.
The specimen stage was moved up 3.2 mm from the contact position at
a compression speed of 0.5 mm/sec to buckle the specimen. A load
when the specimen stage was moved up 3 mm was used as the
compressive load value.
[0054] (Stickiness)
[0055] In the measurement of stickiness, a plate with a diameter of
8 mm and a thickness of 0.8 mm was used. A jig for the stickiness
measurement was attached to a specimen stage (support) of a creep
meter. A part of the jig was detached, and the specimen was fitted
into a part of the detached jig. Then the jig integrated with the
specimen was attached to the creep meter. The specimen stage was
moved to bring the specimen into contact with a metallic probe
(radius of curvature: 2.5 mm) such that a force of 0.05 N was
applied to the specimen, and the stage was stopped at this
position. About 5 seconds after the stage had been stopped, the
specimen was separated from the probe at a separation speed of 1
mm/sec, and a load applied to the specimen was measured using the
creep meter (RE2-33005S manufactured by Yamaden Co., Ltd.). A value
of stickiness was calculated by subtracting the load after the
probe had been separated from the specimen (the load after
separation) from the maximum load measured. When the stickiness
value was 0 N or more and less than 0.16 N, the specimen was rated
"A". When the stickiness value was 0.16 N or more and less than
0.30 N, the specimen was rated "B". When the stickiness value was
0.30 N or more, the specimen was rated "C".
[0056] (Tensile Test)
[0057] Measurement was performed using a dumbbell-shaped specimen
with a total length (L.sub.0) of 20 mm, a parallel-portion length
(L) of 6 mm, a parallel-portion width (W) of 1.5 mm, and a
thickness of 0.8 mm (see FIG. 2). The specimen was immersed in
water held at a constant temperature of 25.degree. C., left to
stand for 1 minute, and then pulled at a speed of 100 mm/min until
break. The strain at the maximum load (=elongation percentage (%))
was determined using software.
[0058] (Results and Discussion)
[0059] The results for lens-shaped Experimental Examples 1 to 14
are shown in Table 5, and the results for plate-shaped Experimental
Examples 15 to 60 are shown in Tables 6 to 9. As can be seen from
the results in Tables 6 to 9, the degree of hydrolysis can be
reduced by increasing the number of methacrylate structural units,
and alkoxymethacrylates are suitable for the methacrylate
component. In the compositions of Experimental Examples 1 to 6 in
Table 5, the amounts of acrylates (POEA and EA) used as a base
material are less than those in the composition described in PTL 1,
and POEMA, EHMA, or LMA is added. In the materials of Experimental
Examples 1 to 3 to which LMA was added, the stickiness was high.
Moreover, the materials were brittle and easily broken, and
glistening occurred easily. In the material of Experimental Example
4 to which EHMA was added, glistening occurred easily. In the
materials of Experimental Examples 5 and 6 to which POEMA was
added, glistening occurred easily, and these materials were hard.
However, in the materials of Experimental Examples 7 to 14 to which
ETMA, which is an alkoxymethacrylate, was added, the stickiness was
low. Moreover, these materials were not brittle.
[0060] In the compositions of Experimental Examples 15 to 17 in
Table 6, the amounts of acrylates (POEA and EA) used as a base
material are less than those in the composition described in PTL 1,
and EMA, BMA, or LMA is added. In the material of Experimental
Example 15 to which EMA was added, the amount of dissolution of
POEtOH was small, and it seemed that the degree of hydrolysis was
reduced, but it was obvious that the intraocular lens material was
not easily folded. In the material of Experimental Example 16 to
which BMA was added, the amount of dissolution of POEtOH was small,
and it seemed that the degree of hydrolysis was reduced, but
glistening occurred easily. In the material of Experimental Example
17 to which LMA was added, stickiness was high. Moreover, the
material was brittle and easily broken, and glistening occurred
easily. In the materials of Experimental Examples to which one of
MTMA or ETMA, which are alkoxymethacrylates, was added, the amount
of dissolution of POEtOH was small, and the degree of hydrolysis
was reduced. Moreover, the stickiness was not high. As in 6, the
occurrence of glistening was low, and the materials were not
brittle.
[0061] As can be seen from the results in Tables 5 to 9, a suitable
amount of the alkoxymethacrylate added is preferably from 10 parts
by mass to 70 parts by mass inclusive and more preferably from 20
parts by mass to 40 parts by mass inclusive based on 100 parts by
mass of the base material. The minimum amount of the
alkoxymethacrylate is preferably within the above range mainly from
the viewpoint of the reduction in the degree of hydrolysis, and the
maximum amount of the alkoxymethacrylate is preferably within the
above range from the viewpoint of ease of folding and from the
viewpoint that no significant burden and difficulty arise during
folding.
[0062] The amount of the aromatic ring-containing acrylate used as
a base material is preferably 30 parts by mass or more based on 100
parts by mass of the base material from the viewpoint that the
intraocular lens material in a hydrated state can have a refractive
index of 1.50 or more. As the refractive index of the material
increases, a thinner lens can be used to obtain a desired
refractive power. The thinner the lens, the more easily the folded
lens can be inserted into an eye.
[0063] The amount of the hydrophilic monomer is preferably 15 parts
by mass or more by the outside ratio based on 100 parts by mass of
the total amount of the base material from the viewpoint of
reducing the occurrence of glistening and is preferably 35 parts by
mass or less by the outside ratio in order that no significant
burden and difficulty arise during folding in a dry state. When the
intraocular lens material in the dry state can be easily bent, the
intraocular lens material can be stored, distributed and used in an
injector device. The compressive load in Table 8 is a value when
the compressive load in Experimental Example 54 is set to 1. The
material of Experimental Example 54 was evaluated in PTL 1, and the
evaluation indicates that this material can be folded, but a large
extra force is necessary. When the compressive load value of a
material is equal to or larger than that of the material of
Experimental Example 54, a determination is made that a significant
burden and difficulty may arise during folding. In Experimental
Examples 50 to 53 shown in Table 8, since ETMA was contained, the
amount of dissolution of POEtOH was small, and the effect of
reducing the degree of hydrolysis was obtained. However, since the
amount of ETMA or HEMA was large, the foldability was not good.
[0064] The amount of the cross-linkable monomer is preferably 2
parts by mass or more by the outside ratio based on 100 parts by
mass of the total amount of the base material from the viewpoint of
reducing the occurrence of glistening and from the viewpoint of
shape recoverability after insertion into an eye and is preferably
4 parts by mass or less by the outside ratio in order to prevent
the elongation of the material to be reduced so that the material
does not break easily.
TABLE-US-00005 TABLE 5 Glistening Specimen Number of the (Lens)
spots.sup.1) Experimental -- example 1 Experimental -- example 2
Experimental 19 example 3 Experimental 35 example 4 Experimental --
example 5 Experimental .infin. example 6 Experimental 4 example 7
Experimental -- example 8 Experimental -- example 9 Experimental --
example 10 Experimental -- example 11 Experimental -- example 12
Experimental -- example 13 Experimental -- example 14
.sup.1)Measurement result with lens Average value of number of
tests (n = 2 or 3)
TABLE-US-00006 TABLE 6 Dissolution Dissolution Dissolution of of of
POEtOH POEtOH POEtOH Refractive index Water (100.degree. C.,
(100.degree. C., (100.degree. C., Glistening 35.degree. C.
Elongation absorption Specimen 30 days) 60 days) 90 days) Number of
Stickiness 25.degree. C. Water percentage percentage (Plate) ppm %
ppm % ppm % the spots.sup.1) --.sup.2) Dry absorption % %
Experimental 1 0.04 4 0.11 3 0.10 -- -- -- -- -- -- example 15
Experimental 2 0.05 4 0.13 5 0.15 10 -- -- -- -- -- example 16
Experimental -- -- -- -- -- -- -- -- -- -- 139 -- example 17
Experimental 3 0.08 8 0.23 15 0.39 2 -- -- -- -- -- example 18
Experimental 6 0.18 40 1.24 192 5.57 2 B 1.523 1.517 -- 1.7 example
19 Experimental 3 0.10 15 0.43 49 1.31 -- -- 1.525 1.519 -- 1.8
example 20 Experimental 2 0.06 7 0.21 15 0.41 0 A 1.527 1.522 --
1.9 example 21 .sup.1)Measurement result by a plate with as
diameter of 6 mm and a thickness of 0.5 mm. Average value of number
of tests (n = 3). .sup.2)A: 0N or more and less than 0.16N, B:
0.16N or more and less than 0.30N, C: 0.30N or more
TABLE-US-00007 TABLE 7 Dissolution Dissolution Dissolution of of of
POEtOH POEtOH POEtOH Refractive index Water (100.degree. C.,
(100.degree. C., (100.degree. C., Glistening 35.degree. C.
Elongation absorption Specimen 30 days) 60 days) 90 days) Number of
Stickiness 25.degree. C. Water percentage percentage (Plate) ppm %
ppm % ppm % the spots.sup.1) --.sup.2) Dry absorption % %
Experimental 6 0.19 43 1.28 205 5.80 -- C 1.523 1.517 -- 1.6
example 22 Experimental 3 0.11 15 0.48 53 1.56 -- -- 1.525 1.519 --
1.8 example 23 Experimental 2 0.06 5 0.16 10 0.27 -- A 1.527 1.521
-- 2.0 example 24 Experimental 6 0.18 43 1.16 209 5.29 -- C 1.523
1.518 -- 1.6 example 25 Experimental 5 0.13 25 0.67 111 2.76 -- --
-- -- -- -- example 26 Experimental 3 0.09 16 0.40 51 1.24 -- --
1.525 1.519 -- 1.8 example 27 Experimental 3 0.09 12 0.32 33 0.86
-- -- -- -- -- -- example 28 Experimental 2 0.05 6 0.16 11 0.28 --
-- 1.527 1.521 345 2.1 example 29 Experimental 5 0.16 36 1.06 162
4.48 -- B 1.522 1.516 -- 2.1 example 30 Experimental 3 0.10 15 0.41
44 1.17 -- B 1.524 1.518 -- 2.4 example 31 Experimental 2 0.06 6
0.17 10 0.28 -- A 1.527 1.521 -- 2.4 example 32 Experimental 5 0.15
33 0.97 150 4.09 -- B 1.522 1.516 -- 2.3 example 33 Experimental 3
0.09 12 0.37 38 1.06 0 B 1.524 1.518 -- 2.2 example 34 Experimental
2 0.06 6 0.18 10 0.29 -- A 1.527 1.520 -- 2.7 example 35
Experimental 6 0.17 38 1.03 176 4.47 -- C 1.522 1.516 -- 2.2
example 36 Experimental 3 0.08 13 0.33 41 0.97 1 B 1.524 1.518 --
2.5 example 37 Experimental 2 0.06 6 0.17 12 0.30 -- A 1.527 1.520
-- 2.8 example 38 .sup.1)Measurement result by a plate with as
diameter of 6 mm and a thickness of 0.5 mm. Average value of number
of tests (n = 3). .sup.2)A: 0N or more and less than 0.16N, B:
0.16N or more and less than 0.30N, C: 0.30N or more
TABLE-US-00008 TABLE 8 Dissolution Dissolution Dissolution of of of
POEtOH POEtOH POEtOH Refractive index Water (100.degree. C.,
(100.degree. C., (100.degree. C., Glistening 35.degree. C.
Compressive absorption Specimen 30 days) 60 days) 90 days) Number
of Stickiness 25.degree. C. Water load percentage (Plate) ppm % ppm
% ppm % the spots.sup.1) --.sup.2) Dry absorption --.sup.3) %
Experimental 3 0.09 13 0.36 37 0.95 -- A 1.524 1.517 -- 3.1 example
39 Experimental 2 0.06 6 0.18 10 0.27 -- A 1.526 1.520 -- 3.3
example 40 Experimental 2 0.06 5 0.16 7 0.19 -- -- 1.520 1.512 --
-- example 41 Experimental 2 0.05 4 0.13 3 0.10 -- -- 1.514 1.507
-- -- example 42 Experimental 2 0.06 5 0.13 4 0.10 -- -- 1.509
1.500 0.7 -- example 43 Experimental 1 0.04 3 0.09 1 0.02 -- --
1.503 1.495 -- -- example 44 Experimental 2 0.07 10 0.29 29 0.79 1
A 1.524 1.517 -- 3.0 example 45 Experimental 2 0.05 5 0.16 8 0.23
-- A 1.526 1.520 -- 3.1 example 46 Experimental 3 0.09 13 0.34 36
0.88 -- B 1.524 1.517 -- 3.0 example 47 Experimental 2 0.06 6 0.17
11 0.29 -- A 1.526 1.519 -- 3.2 example 48 Experimental 2 0.06 6
0.19 10 0.28 -- -- -- -- 0.8 -- example 49 Experimental 2 0.06 5
0.15 6 0.17 -- -- 1.520 1.510 1.1 -- example 50 Experimental 2 0.05
4 0.12 4 0.10 -- -- 1.514 1.504 1.3 -- example 51 Experimental 2
0.07 7 0.19 12 0.29 -- -- -- -- 1.8 -- example 52 Experimental 2
0.06 6 0.18 8 0.23 -- -- -- -- 1.6 -- example 53 Experimental -- --
-- -- -- -- -- -- -- -- 1.0 -- example 54 .sup.1)Measurement result
by a plate with as diameter of 6 mm and a thickness of 0.5 mm.
Average value of number of tests (n = 3). .sup.2)A: 0N or more and
less than 0.16N, B: 0.16N or more and less than 0.30N, C: 0.30N or
more .sup.3)Each value of experimental examples is standardized by
determining the compressive load of experimental example 54 as
"1".
TABLE-US-00009 TABLE 9 Dissolution of Dissolution of Dissolution of
POEtOH POEtOH POEtOH (100.degree. C., (100.degree. C., (100.degree.
C., Specimen 30 days) 60 days) 90 days) (Plate) ppm % ppm % ppm %
Experimental 5 0.14 24 0.66 91 2.33 example 55 Experimental 5 0.15
31 0.83 134 3.33 example 56 Experimental 5 0.13 23 0.61 79 1.92
example 57 Experimental 4 0.14 28 0.82 119 3.31 example 58
Experimental 5 0.13 23 0.60 79 1.96 example 59 Experimental 3 0.09
11 0.30 25 0.63 example 60
[0065] The present application claims priority from Japanese Patent
Application No. 2016-148426 filed on Jul. 28, 2016, the entire
contents of which are incorporated herein by reference.
INDUSTRIAL APPLICABILITY
[0066] The invention disclosed in the present description can be
used for intraocular lens applications.
REFERENCE SIGNS LIST
[0067] 10 indenter,
[0068] 11 jig,
[0069] 12 specimen.
* * * * *